Individual performance optimization of electronic lens for presbyopia correction

ABSTRACT

An optimization system for presbyopia correction includes a dynamic lens and a separately disposed controller. The dynamic lens includes a sensor measuring an ocular element of a person&#39;s eye, a control electronics, an actuator, and a presbyopia correcting optical element communicating with the actuator for its setting to a far or near optical power. The controller sends paired instructions synchronically to the person as an audio command for viewing the object at far or near distance and to the control electronics as a wireless command to send the actuation signal to the actuator for communication with the presbyopia correcting optical element. The control electronics receives the wireless command and the sensor signal, stores the sensor signal, sends the actuation signal to the presbyopia correcting optical element and stores the corresponding actuation signal. The actuation signal communicates to the presbyopia correcting optical element to set for far or near optical power.

CROSS-REFERENCE TO RELATED APPLICATIONS

This non-provisional application claim priority from U.S. ProvisionalPatent Applications: Ser. No. 62/970,100 filed Feb. 4, 2020; Ser. No.62/981,534 filed Feb. 26, 2020; Ser. No: 62/983,753 filed Mar. 2, 2020,the entire contents of which are fully incorporated into the presentapplication with this reference.

DESCRIPTION Field of the Invention

The present invention relates generally to a presbyopia correcting lensthat changes its optical power by a surface shape, material refractiveindex or relative movement of a lens parts under the action of an ocularelement of the eye. More particularly, it relates to an electronicpresbyopia correcting ophthalmic lenses such as eyewear lens (EL),intraocular lens (IOL) and contact lens (CL) that change their opticalpower with optical surface shape, optical material refractive index,and/or a relative movement of lens parts. In addition, the presentinvention relates to a wireless communication by presbyopia correctingophthalmic lens for individual performance optimization.

Background of the Invention

Ophthalmic lenses disclosed in this application refer to eyewear lenses(EL) installed in front of the eye at the spectacle frame, intraocularlenses (IOL) refer to those that are installed inside the eye andcontact lens (CL) refer to those installed at the front surface of theeye.

There are several applications of visual correction such as a low visionaid for visual impairment where a visually impaired patient requires amagnified image and presbyopia correction for viewing at far and neardistances. This application will reference to presbyopia correction forexplaining the invention with the understanding that the invention isfully application to a low vision aid where optical power change is usedfor switching between magnified and normal imaging or between imagingwith different magnifications.

A development of ophthalmic lens with variable foci has been a subjectof many innovations. Fluidic balloon type IOL where optical power varieswith stretching and squeezing fluidic balloon, is described by:Salahieh, et al. in U.S. Pat. No. 10,548,718; Brady, et al. in U.S. Pat.No. 10,485,654; and de Juan, Jr., et al. in U.S. Pat. No. 10,285,805,the contents of which are fully incorporated herein with this reference.Supporting element and optical body of fluidic balloon IOL have beendescribed as one piece or two-piece structure where the optical body isa replaceable part. The fluidic balloon application to contact lens (CL)has been described by Egan, et al. in the U.S. Pat. No. 9,500,884, thecontents of which are fully incorporated herein with this reference.Fluidic balloon type Eyewear lenses have been also produced.

Alvarez type IOL design where wave plates are mutually shiftingperpendicularly to the optical axis of the lens, is described byRombach, et al. in the U.S. Pat. No. 10,463,473, the contents of whichare fully incorporated herein with this reference. This type of IOL andfluidic balloon IOL are called accommodating IOLs (AIOL). Fluidicballoon type contact lens is called adjustable or variable CL. Alvareztype eyewear lenses are produced by the Adlens® company and others.These types ophthalmic lenses are called “analog dynamic lens” as theiroptical power changes in a continuous fashion between far and near.

Switching between optical powers to create a binary system of twooptical powers is described by Portney in the U.S. Pat. No. 9,364,319for application to IOL, contact lens and eyeglasses, the contents ofwhich are fully incorporated herein with this reference. The opticalpower switching occurs by changing between refractive and diffractivesurface shapes. The option to use electro-active material for switchingbetween optical powers is described by: Okada, et al. in the U.S. Pat.No. 4,919,520; Haddock, et al. in the U.S. Pat. No: 8,523,354; Lin, etal. in the U.S. Pat. No. 10,613,350 and others, the contents of whichare fully incorporated herein with this reference. These types ofophthalmic lens are called switchable ophthalmic lens or “digitaldynamic lens.”

Analog and digital dynamic lenses together are called “dynamic lens” astheir optical powers are dynamically changing within certain rangewithin some finite area of the optic, usually 3-5 millimeters diameterof the optical body in case of IOL and CL and about 15 mm in case ofeyewear lens in spectacle. Accommodating and switchable IOL are called“dynamic IOL,” and variable and switchable CL are called “dynamic CL.”An eyewear lens within a spectacle that changes its power within afinite area is called a “dynamic eyewear lens” or “dynamic EL”

Wireless communication of a dynamic lens with an electronic device hasbeen described by: Winoto in U.S. Pat. No. 10,602,513; Amirparviz, etal. in U.S. Pat. No. 8,096,654; Portney in U.S. Pat. No. 9,931,203;Youssef in the U.S. Pat. No. 10,409,092; Basinger, et al. in U.S. Pat.No. 10,076,408; Galstian, et al. in U.S. Pat. No. 10,561,492; Lewis inU.S. Pat. No. 8,733,928; Thomas, et al. in U.S. Pat. No. 7,792,552 andothers, the contents of which are fully incorporated herein with thisreference. These patents disclosed electronic eyewear lens, IOL and CLwirelessly communicate with external electronics. They also included asensor to determine when and how much to accommodate, i.e. to changeoptical power.

Nevertheless, the issue remains in providing far and near foci optimizedfor any given individual wearer because a sensor signal may varysignificantly depending upon a dynamic lens placement, anatomicalfeatures of the wearer, physiology of ocular element interaction with itby the dynamic lens results in an optical power change. The optioncurrently used involves a wearer to continually control a signal forpower change which is inconvenient, deferring a wearer from other tasksand prompt to delay of the focusing itself. The goal of the presentdisclosure is to optimize a presbyopia correcting lens for any givenwearer regardless of a dynamic lens placement, anatomical features ofthe wearer, physiology of ocular element responsible for the opticalpower change. Thus, it would be desirable to provide method and deviceswhich address the above deficiency and weaknesses current electronicallycontrolled dynamic lenses in achieving individual performanceoptimization for a presbyopia correction.

SUMMARY OF THE INVENTION

The primary focus of dynamic lens application is a presbyopiacorrection, the analogous dynamic lens can be applied to low visionmagnification where an optical power change is substantially higher thanin presbyopia correction. The latter is commonly up to about 3 D (Dstands for diopter) in spectacle plane and low vision magnification isabout 5 D-10 D to provide 1.5×-2.5× magnification though Add power mightbe even higher to provide higher magnification but the correspondingreduction in reading distance becomes a limiting factor. As the onlydifference between presbyopia correction and low vision magnification isthe difference in Add powers in switching between the optical states oraccommodation, the reference only to presbyopia correction will be usedwith the understanding that it includes also low vision magnification.

An optimization system for presbyopia correction in accordance with thepresent invention consists of dynamic lens and controller where dynamiclens can be eyewear lens (EL), intraocular lens (IOL) and contact lens(CL). Generally, it may also include any implantable in the eye lens.They are called correspondently dynamic EL lens, dynamic IOL and dynamicCL.

A dynamic lens includes a “sensor” to detect ocular element state forfocusing on an object at far distance, near distance and possiblyintermediate distance and an “actuator” to change optical power to “faroptical power”, “near optical power” or “intermediate optical power” tobring an object at each corresponding far, near and intermediatedistances in-focus. The far distance is defined as 2 meters (about 6.5feet) from the eye and beyond, the near distance is defined as 0.5 meter(1.64 feet) from the eye and closer, and intermediate distance isdefined as the distance between 0.5 meter (1.64 feet) and 2 meters(about 6.5 feet). (In an alternative embodiment designed to simplify thedevice by removing the intermediate distance, one may also define thefar distance as 2 meters and beyond whereas the near distance is definedas less than 2 meters.) Dynamic lenses also include “controlelectronics” to take a signal from the sensor as the input signal andmodify it appropriately for the output to the “actuator” to actuate a“presbyopia correcting optical element” of the dynamic lens to arequired optical power that brings a viewed object in-focus. Theactuator may include an actuation chamber connected with SBS opticalelement or fluidic balloon or a fluidic chamber to move one of the waveplates in Alvarez type design of the presbyopia correcting opticalelements. The actuator may be an electronic one to produce electricfield that controls a presbyopia correcting optical element made of anelectro-active material. Both types of actuators are included in thepresent disclosure and are simply called “actuator(s).” “Optimizationsystem for presbyopia correction” includes a sensor, a controlelectronics with the actuator and a presbyopia correcting opticalelement.

A sensor of a dynamic lens is selected to measure a difference in aneffect of an ocular element of an eye on the sensor when changingviewing objects between far and near distances. In case of an eyewearlens, the ocular element is the front surface of the eye and a sensor isan IR detector to measure a change in infrared light intensity reflectedoff the front surface of the eye with a change in eye gaze directionwhen viewing between far and near distances. For instance, betweendownward gaze for an object at near distance and straight-ahead gaze foran object at far distance. Another option is to measure a change in eyesconvergence in binocular vision between viewing objects at differentdistances. Convergence is defined as simultaneous inward movement ofboth eyes and eyes convergence increases with closest object. In case ofIOL, ocular element is the ciliary body containing ciliary muscle and asensor is a pressure sensor or bend sensor to measure changes of theciliary muscle effect on the dynamic IOL between ciliary musclecontraction for viewing an object at near distance and relaxation forviewing an object at far distance. In case of CL, the ocular element isthe lower eyelid and a sensor is a pressure sensor to measure changesbetween downward gaze in viewing an object at near distance andstraight-ahead gaze in viewing an object at far distance.

An option is to have the universal sensor in a form of sensor cell asdescribed by Portney in the U.S. Pat. No. 9,931,203, to directly measurechanges in ciliary muscle contraction and relaxation. The measuredeffect can be a pressure change or electromyographic signal change withthe ciliary muscle activity. Thus, the ciliary muscle is the ocularelement in this case.

An external electronic device is called controller. It is another partof the optimization system for presbyopia correction. It can be a standalong electronic device or smart phone with the correspondingapplication. The controller is to be used by a medical provider orwearer of a dynamic lens for “teaching” the dynamic lens to synchronizea range of sensor signals when viewing an object at a certain distance(far, near, intermediate) where a range of sensor signal is caused by apractically occurred variation in gaze directions of the wearer. Avariation of gaze directions may be created by moving a viewing objecton a screen placed at a certain distance from the eye (far, near orintermediate) where the object moves right, left, up and down withoutturning a wearer's head or by viewing a stationary object at a certaindistance and turning head right, left, up and down. The controller atthe same time instructs the control electronics to output the actuationsignal that effects a presbyopia correcting optical element of thedynamic lens to bring the corresponding viewing object in-focus.

The “learning” program of the control electronics of the dynamic lensstores ranges of sensor signal and corresponding actuation signals in aform of matrix to run for an object at far distance, near distance, andpossibly, intermediate distance. This process of “teaching” the dynamiclens to optimize individual performance for presbyopia correction is the“optimization mode.” Upon completion of the optimization mode the“operation mode” follows. In the operation mode the “learning” programof the control electronics identifies a sensor signal to belong to acertain range of sensor signals to provide the corresponding actuationsignal for the presbyopia correcting optical element to bring a viewingobject in-focus. In the absence of the optimization mode, a wearer mustconstantly control a dynamic lens in providing required optical powerfor bringing an object in-focus or rely on a dynamic lens clinical trialstatistical outcome which might not provide necessary actuation signalsrequired for a given wearer focusing needs.

In one preferred embodiment of the current invention, the optimizationsystem for presbyopia correction includes a sensor, a controlelectronics, an actuator and a presbyopia correcting optical element ofthe dynamic lens, and a controller with a “teaching program”. Thecontroller “teaching” program provides paired instructions to a wearerof the dynamic lens and control electronics of the dynamic lens. In thispreferred embodiment, audio instructions to the wearer instruct tochange gaze direction to an object at one of far and near distances byslightly turning the head right, left, up and down when viewing theobject thus producing different sensor signals that form a “range ofsensor signal at far” if the viewing object is at far distance or a“range of sensor signal at near” if the viewing object is at neardistance. The wireless instruction of the paired interactions of thecontroller communicates with the control electronics of the dynamic lensto output the activation signal for far as the wearer is instructed toview an object at far distance or activation signal for near as thewearer is instructed to view an object at near distance. Thecorrespondingly coupled sensor ranges and activation signals form the“matrix for far” and “matrix for near” stored by the control electronicsas the outcome of “teaching” program operation of the optimization mode.Both matrices form a “matrix” used by the control electronics in theoperation mode to control optical power of the presbyopia correctingoptical element between “far optical power” or “near optical power”. Inthe operation mode a received sensor signal from an interaction betweenthe dynamic lens and ocular element is compared with the matrix togenerate the appropriate actuation signal for presbyopia correctingoptical element to keep or bring the viewing object in-focus.

Wireless signal by the controller can be WiFi, LiFi, Bluetooth, NFC orany other type of remote communication. An instruction by the “teaching”program to a wearer is an audio instruction either directly by thecontroller to the wearer or indirectly via a medical provider who relaythe instructions vocally to the wearer. Thus, paired instructions, oneto the wearer and another to the control electronics of the dynamic lensis given by the controller. The teaching program goes over a sequence ofpaired instructions over different gaze directions at different objectsdistances, usually at far and at near. It may include repetitions ofgaze direction at each distance to collect more accurate range of sensorsignal at each distance. The outcome of the optimization mode is thematrix between sensor ranges and activation signals at differentdistances. In the operation mode, the “learning” program of the controlelectronics operates the dynamic lens according to the algorithm thatrelies on the matrix to determine which range of sensor signal areceived sensor signal belongs to and synchronize the actuation signalwith the received sensor signal for the presbyopia correcting opticalelement to bring an object at the corresponding distance in-focus. Theresult is a robust response of the presbyopia correcting optical elementfor a given wearer of the dynamic lens. In case of ranges overlapping,say, near and intermediate or intermediate and far, the learning programalgorithm calculates a likely range of sensor signal the sensor signalfalls in or wirelessly communicate to the controller to instruct thewearer to limit a range of movement in a certain way.

In terms of powering the described above devices, the followingdiscussion is relevant. The latest lithium-ion microbattery can be 2×2mm size and down to 10 microns thick. One option is the EnerChip™ byCymbet™ which is a thin film rechargeable solid-state smart batteries(SSB). In this case a millimeter-sized CBC910 can be integrated withmicroelectronics into a single package. Another option is a photocell asa power source which may be combined with a capacitor for energystorage. For instance, micro solar cell by Sandia™ can be 0.25millimeter in diameter and ≈20 micrometers thick and the efficiencysimilar to conventional cells of ≈14.9%. It can generate ≈0.3 Joule ofelectric energy with 12 hours light exposure. Another option is atransparent photovoltaics (PV) developed by Ubiquitous Energy™. Ittransmits visible light while capturing ultraviolet (UV) andnear-infrared (NIR) light with efficiency over 10%. The transparency isthe greatest advantage to allow the increase in effective area of thephotocell without effecting device aesthetics. Besides, it includesnon-toxic materials and, therefore, offers a great potential for theintraocular lens and contact lens. Another option is inductiverecharging of electric power either by environment or external dedicatedelectro-magnetic emission sources which might be particularly useful foreyewear lens energy recharging. It is also important to note thatsilicon semiconductors are commonly used but semiconductor power devicesbased on gallium nitride (GaN) may be a displacement for the technologyas it conducts electrons more than 1000 times more efficient thansilicon thus allowing for smaller sizes with lower manufacturing cost.

Another embodiment of the current invention is an optimized actuatorfluidic based presbyopia correcting optical element and will be shown onthe example of surface based switchable (SBS) dynamic lens disclosed byPortney in the U.S. Pat. No. 9,364,319. Such an actuator is to consume aminimum of energy. This is particularly critical for a dynamic IOL butis also highly beneficial for a dynamic eyewear lens and dynamic CLbecause of a battery recharging or replacement might not be readilyavailable or inconvenient.

SBS dynamic lens manifests 2-states, one is near focus and another farfocus. The corresponding optimum actuator is a bi-state actuator thatswitches between 2 stable states, where a stable state is the state thatthe actuator maintains without a use of electric energy. The electricenergy is only required for switching between the stable states. Suchoptimum actuator has n-morph piezoelectric bender with “n” piezoelectriclayers (n≥2) for bending piezoelectric bender under a voltageapplication into two opposite directions. Commonly, bimorph bender isused with two piezoelectric layers. One end of the bender is fixed atthe “flexible anchor” and at the other end, “deflection end,” is alloweddeflection in one of the opposite directions between two permanentmagnets. The deflection end of the bender includes magnetically activematerial to attract it to one of the magnets as it comes into proximityto it upon bending under applied voltage. The bender then is kept in itsunbent position with the one end at one permanent magnet and another endat the flexible anchor upon the voltage termination—this is one stableposition of the piezoelectric actuator. As the voltage is applied tobend the bender in the opposite direction, the deflection end displacesto a proximity of other permanent magnet. The bender then is kept in thesecond position with the one end at the second permanent magnet andanother end at the flexible anchor upon the voltage termination—this issecond stable position of the piezoelectric actuator. An actuationchamber is attached to the bender and chamber volume changes between twostable positions of the bender. The transported amount of fluid betweenthe actuation chamber and SBS optical element required for switchingbetween two optical powers is defined by the actuation volume changebetween two stable conditions of the bi-stable actuator.

The described bi-stable actuator can be also applied to an analogdynamic lens such as fluidic balloon and one based on Alvarez designwhere a fluid chamber moves one of the wave plates. In this case, theanalog continuous change in optical power becomes 2-state opticalelement where the optical power continuous change between two opticalpowers with bi-state actuator switching between its two stable states.

Features and advantages of the present invention will become apparentfrom the following more detailed description, when taken in conjunctionwith the accompanying drawings, which illustrate, by way of example, theprinciples of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings illustrate the invention. In such drawings:

FIG. 1 shows a block diagram of individual performance optimizationmethod for an electronic dynamic lens that is applied to dynamic Eyewearlens, dynamic IOL and dynamic CL.

FIG. 2A through FIG. 2C describe applications of individual performanceoptimization method to dynamic eyewear lens.

FIG. 3 describes application of individual performance optimizationmethod to dynamic IOL.

FIG. 4 describes application of individual performance optimizationmethod to dynamic CL.

FIG. 5A through 5D demonstrate bi-state piezoelectric actuator operationin providing 2 stable states where the electric energy is consumed onlyfor switching between the states.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

FIG. 1 shows a block diagram of individual performance optimizationmethod for an electronic dynamic lens that is applied to dynamic eyewearlens, dynamic IOL and dynamic CL. The corresponding “optimizationsystem” consists of controller 100 and dynamic lens that includes sensor130, control electronics 140, actuator 150 and presbyopia correctingoptical element 160. The controller 100 provides paired synchronizedinstructions to a wearer 110 as shown by line 1 a and controlelectronics of the dynamic lens as shown by line 1 b. Actuator 150controls presbyopia correcting optical element 160 of the dynamic lensto change its optical power. Sensor 130, control electronics 140,actuator 150 and presbyopia correcting optical element 160 are all partof the dynamic lens.

Controller 100 provides audio instruction to a wearer 110 to view anobject at certain distance with certain gaze direction. It may alsoinstruct the wearer what object to use for the viewing. Synchronically,the controller 100 wirelessly instructs the control electronics 140 tooutput actuation signal (electric voltage, for instance) to the actuator150 as shown by line 5, that takes the presbyopia correcting opticalelement 160 to an optical power that brings the viewing object in-focus,as shown by line 6. If the controller instructs wearer 110 of thedynamic lens to view the object at far distance, the instruction to thecontrol electronics 140 is to output the “actuation signal for far” forthe presbyopia correcting optical element 160 to provide “far opticalpower” that brings far object in-focus. If the controller instructswearer 110 of the dynamic lens to view the object at near distance, theinstruction to the control electronics 140 is to output the “actuationsignal for near” for the presbyopia correcting optical element 160 toprovide “near optical power” that brings near object in-focus. If thecontroller instructs wearer 110 of the dynamic lens to view the objectat intermediate distance, the instruction to the control electronics 140is to output the “actuation signal for intermediate” for the presbyopiacorrecting optical element 160 to provide “intermediate optical power”that brings intermediate object in-focus.

The dynamic lens of the wearer interacts with the corresponding ocularelement 120 as shown by line 2. Ocular element is such that theinteraction with it varies with the wearer viewing objects at differentdistances at far and near and change in gaze directions when viewingsuch objects. An interaction between the dynamic lens and ocular element120 and a change in interactions are measured by the sensor 130 as shownby line 3. A type of interaction and type of sensor vary for differenttype of dynamic lens and will be described below. An interaction isconverted by the sensor 130 into input electric signal to the controlelectronics 140 as shown by line 4. The signal shown by line 4 is calledthe “sensor signal.” Depending upon dynamic lens installation inreference to the eye, anatomy and physiology of the eye, the interactionand sensor signal varies between different wearers.

The method used by the optimization system for individual performanceoptimization is to establish a range of sensor signals of an individualwearer, so called “range of sensor signal” that produces an activationsignal that brings a viewing object in-focus for this individual wearer.A range of sensor signal is established for each distance being far,near and, possibly, intermediate, and they are called correspondently“range of sensor signal at far”, “range of sensor signal at near” and“range of sensor signal at intermediate.” Correspondently, the controlelectronics 140 produces “actuation signal for far”, “actuation signalfor near” and “actuation signal for intermediate” that results incorrespondent “far optical power”, “near optical power” and“intermediate optical power” by the presbyopia correcting opticalelement 160. The range of sensor signal is established for a practicalrange of gaze directions of the wearer when viewing an object at aspecified distance. Changes in gaze directions are created by the wearerslightly turning head right, left, up and down when viewing the objectat the specified distance, i.e. an object at far distance, an object atnear distance or object at intermediate distance. The process involvespractical conditions of head positions when viewing an object at eachdistance. In cases where ranges of sensor signals overlap, the controlelectronics may provide a wireless feedback to the controller toinstruct the wearer on a limit in some gaze directions to provide arobust performance of the dynamic lens, for instance to limit down gazewhen viewing far object or limit upper gaze when viewing a near objectin case of dynamic eyewear lens or dynamic contact lens.

During this “optimization mode,” a “teaching” program of the controllergoes over a certain sequence of paired interactions to instruct thewearer on changes in gaze directions for an object at a given distanceand a “learning” program of the control electronics stores a matrix thatcorrelates a range of sensor signal and actuation signal for the samedistance, i.e. actuation signal for far corresponds to a range of sensorsignal at far, actuation signal for near corresponds to a range ofsensor signal at near and actuation signal for intermediate correspondsto a range of sensor signal at intermediate. In the operation mode, thedynamic lens operates independently of the controller in the operationmode where the learning program of the control electronics 140 follows aprogram algorithm to analyze a sensor signal received by the controlelectronics to provide an actuation signal that brings a viewing objectin-focus. Thus, the optimization mode establishes individual performancefor presbyopia correction for an unique dynamic lens installation at thewearer eye and unique anatomy and physiology of the wearer of thedynamic lens.

FIG. 2A shows an example of optimization system of dynamic eyewear lens.It includes a controller 105 and dynamic eyewear lens 180 framed at thespectacles 155. Dynamic eyewear lens 180 is the right lens of thespectacles 155, left eyewear lens is a mirror image of the right eyewearlens 180 and, therefore, only right dynamic eyewear lens 180 isdescribed. The eyewear lens 180 includes upper presbyopia correctingoptical element 190 and lower presbyopia correcting optical element 200.As an example, SBS optical element is used for both elements but theycan be any types of dynamic lens being fluidic balloon, Alverez type orelectro-active material that changes refractive index under electricfiled. SBS optical element 190 switches between far and intermediateoptical powers and SBS element 200 switches between far and near opticalpowers. The dynamic eyewear lens 180 includes infra-red (IR) emitters250 and 270 and IR sensors 230 and 260. The sensors are connected to thecontrol electronics 215 to provide input signal on eye tracking, i.e. achange in gaze direction. The front surface of the eye is the ocularelement for the dynamic eyewear lens, where, as the eye's gaze directionchanges an interaction of the ocular element with the sensor 230 and/or260 changes where interaction is a flux of the IR light measured by theIR sensor upon IR light reflection off the ocular element of the eye.The dynamic eyewear lens 180 also includes actuator 210 for SBS opticalelement 200 and actuator 220 for SBS optical element 190, both connectedto the control electronics 215 to receive its output signal to actuatethe corresponding presbyopia correcting optical elements 190 and 200.

Paired instructions as shown by line 3 a is provided by the controller105. The wearer audio instruction requires the wearer to look at the farobject with straight ahead gaze as indicating by the visual axis 170 ofthe wearer's right eye 165. The visual axis 170 passes through the SBSoptical element 190. At least one of the sensors 230 and 260 or bothprovide “sensor signal” as input signal to the control electronics 215.The wireless instruction for control electronics 215 commands it tooutput “activation signal for far” to the actuators 220 and 210 toswitch SBS optical elements 190 and 200 to “far optical power.” Thecorresponding sensor signal is stored by a “learning” program of thecontrol electronics 215. The “teaching” program of the controller 215sends another paired instructions to require the wearer to view the farobject with straight ahead gaze but slightly turning head to the right.The process is repeated and the control electronics 215 stores thecorresponding sensor signal. The process is repeated with head turningslightly left, up, down, and the process may be repeated. The set ofsensor signals results in a “range of sensor signal at far” togetherwith the “actuation signal for far” form the matrix that is stored bythe “learning” program of the control electronics 215. This allows forthe wearer's dynamic lens robust operation in viewing an object at fardistance because the range of sensor signal at far covers signal valuesthat practically occurs when viewing far object with an eyewear lens.The program of the control electronics 215 runs an algorithm thatoutputs activation signal for far to both presbyopia correcting opticalelements 190 and 200 to provide far optical power to bring the farobject in-focus.

FIG. 2B shows an example of optimization system including a controller105 and dynamic eyewear lens 180′ framed at the spectacles 155 wherepaired instructions are shown by line 3 b. The instruction to a weareris to view a near object with downward gaze as indicating by the visualaxis 170′ with downward angle “a” from the visual axis 170 of thewearer's right eye 165. The visual axis 170′ passes through the SBSoptical element 200′. At least one of the sensors 230 and 260 or bothprovide “sensor signal at near” as input signal to the controlelectronics 215. The wireless instruction to the control electronics 215instructs it to output “activation signal for near” to actuator 210 toswitch SBS optical element 200′ to near optical power. The sensor signalis stored by the control electronics 215. The “teaching” program of thecontroller 105 sends another paired instruction to require the wearer toview the near object with slightly turning head right, left, up anddown. The process may be repeated and the control electronics 215 storesthe corresponding “range of sensor signal at near.” The set of sensorsignals results in a “range of sensor signal at near” together with the“actuation signal for near” form the matrix that is stored by the“learning” program of the control electronics 215. This is theoptimization mode for the electronic dynamic eyewear lens with thecontroller producing paired instructions of audio command to a wearerand wireless command to control electronics where both reference to theone of the “far” and “near” distances by wearer's viewing and producingoptical power. In the operation mode a sensor signal falls within therange of sensor signal at near, the control electronics algorithmoperates an algorithm over the matrix to output the actuation signal fornear to bring near object in-focus. If the ranges of sensor signal atfar and near overlap, the control electronics instructs the controller105 on the overlap between certain gaze directions and the controllerinstructs the wearer to limit gaze directions in a corresponding plane,likely head down in far viewing and head up in near viewing.

FIG. 2C shows an example of optimization system including a controller105 and dynamic eyewear lens 180″ framed at the spectacles 155 where apaired instruction as shown by line 3 c is provided by the controller105 for an object at intermediate distance. The instruction to wearer isto view an object at intermediate distance with both eyes. Binocularviewing creates convergence with a gaze direction by the right eye 165indicated by the visual axis 170″ with its angle of convergence “β” tothe visual axis 170. The visual axis 170″ passes through the SBS opticalelement 190′. At least one of the sensors 230 and 260 or both provide“sensor signal at intermediate” as input signal to the controlelectronics 215. The wireless instruction to the control electronics 215commands it to output “activation signal for intermediate” to theactuator 220 to switch SBS optical element 190′ to intermediate opticalpower. The “teaching” program of the controller 215 send another pairedinstructions to require the wearer to view intermediate object withslightly turned head to the right and the process is repeated. Theprocess is repeated with head turning slightly left, up, down, and soon. The same as above, a set of sensor signals results in a “range ofsensor signal at intermediate” together with the “actuation signal forintermediate” form the matrix that is stored by the “learning” programof the control electronics 215. If the ranges of sensor signal at farand intermediate or intermediate and near overlap, the controlelectronics instructs the controller 105 on the overlap between certaingaze directions and the controller instructs the wearer to limit gazedirections in a corresponding plane. In the operation mode as a sensorsignal falls within the range of sensor signal at intermediate, thecontrol electronics algorithm operates an algorithm over the matrix tooutput the actuation signal for intermediate to bring the intermediateobject in-focus. Same as above, the control electronics communicationswith the controller on ranges overlap for wearer instruction on thelimits in gaze directions for robust dynamic lens performance.

FIG. 3 shows an example of optimization system for electronic dynamicIOL. It includes a controller 205 and dynamic IOL 300 supported by theocular element 310 in the form of ciliary body that includes ciliarymuscle. The dynamic IOL 300 is shown with two supporting members 330 and340 but may include any number of supporting members. Supporting member330 includes pressure sensor 350 at its very periphery, supportingmember 340 includes pressure sensor 360 at its very periphery, both tomeasure pressure produced by the ciliary body/ciliary muscle 310 incontraction for accommodation in viewing an object at near distance andrelaxation for disaccommodation in viewing an object at far distance.Another option is to include bending sensors 390 and 400 to detectsupporting members bending with ciliary muscle contraction andrelaxation. Pressure sensors and/or bend sensors might be self-poweredsensors based on piezoelectric or triboelectric nanogenerator as thepresent days nanogenerator may produce a voltage of 1.63 V and a powerof 0.03 μW. The sensor signal from the sensors is the input to thecontrol electronics placed at the electronics compartment 370. Power andpower electronics may be in the same compartment 370. An actuationsignal is the output of the control electronics to the actuator, forinstance, a piezo-electric bi-state actuator placed at the actuatorcompartment 380. The dynamic IOL optical body 320 includes presbyopiacorrecting optical element 410. As an example, SBS optical element isused for switching between far and near optical powers but other typesof design such as material based switching using electro-activematerials, fluidic balloon design or Alvarez type design can be used.

The controller 205 provides paired instructions as shown by line 3′, oneis audio instruction for the wearer and another wirelessly to thecontrol electronics of the dynamic lens 300. The following descriptionis provided using SBS optical element as an example of presbyopiacorrecting optical element. The wearer's audio instruction requires thewearer to view either far or near object. The ocular element interactswith a sensor or sensors to provide correspondently “sensor signal atfar” or “sensor signal at near” as input signal to the controlelectronics. The wireless instruction by the controller 205 to thecontrol electronics commands it to output correspondently “activationsignal for far” or “activation signal for near” to the actuator toswitch SBS optical element 410 to the corresponding “far optical power”to bring the object at far distance in-focus or “near optical power” tobring the object at near distance in-focus. The “teaching” program ofthe controller 205 follows a certain algorithm to change gaze directionsby instructing the wearer to turn their head slightly when viewing theobject at far distance and the object at near distance. Correspondently,the “learning” program of the control electronics collects “range ofsensor signal at far” and “range of sensor signal at near” to form amatrix to gather with the corresponding “activation signal for far” and“activation signal for near.” This is the optimization mode for theelectronic dynamic IOL with the controller producing paired instructionsof audio command to a wearer and wireless command to control electronicswhere both reference to the one of the “far” and “near” distances bywearer's viewing and producing optical power. The control electronicsthen operates the matrix under an algorithm to place a sensor signal atan appropriate range of sensor signal and output the appropriateactuation signal for the presbyopia correcting optical element toproduce appropriate optical power that brings a viewing object in-focusfor the given wearer. This is equivalent to the optimization mode andoperation by the dynamic eyewear lens of FIG. 2A-2C and described belowdynamic contact lens of FIG. 4.

If a sensor signal has a resolution to measure interaction with ocularelement at intermediate viewing from near and far viewing, and apresbyopia correcting optical element has a capability for intermediateoptical power in addition to far and near, the optimization mode runsthe paired instructions for intermediate viewing and producingintermediate optical power. Then the “learning” program of the controlelectronics will store a matrix for intermediate that correlates “rangeof sensor signal at intermediate” and “actuation signal forintermediate” to be used in operation by the dynamic IOL. The same isapplicable to a dynamic eyewear lens of FIG. 2A-2C and dynamic CL ofFIG. 4.

The FIG. 4 shows an example of optimization system for electronicsdynamic CL. It includes a controller 205′ and dynamic CL 420. Thedynamic CL 420 consists of optical element 440 of about 7 mm diameterand supporting member 430 which includes prism ballast 450 withtruncation in combination with others features of the supporting member430 such as thin zones (also known as double slab-off) and so on. Theballast 450 is for effective interaction with the lower eyelid 460 whichis the ocular element of the dynamic CL 420. The ballast 450 is also formaintaining dynamic CL orientations on the eye. The ballast is commonlyused in translating (alternating) contact lenses. The overall sizing islike the one used in segmented and progressive CL designs to insure lensgood centration and minimum displacement. Optical element 440 includespresbyopia correcting optical element 490. As an example, SBS opticalelement is used where SBS optical element 490 switches between far andnear optical powers. The presbyopia correcting optical elements can bealso of other designs such as material based switching usingelectro-active materials, fluidic balloon design or Alvarez type design.The ballast 450 includes control electronics 470 connected with apressure sensor 510 at the lower edge of the ballast to measure apressure exerted by the ocular element 460 on the ballast. The ballast450 also includes actuator 480 for to actuate a presbyopia correctingoptical element to different optical powers, in this case the SBSoptical element 490 via a channel 500. The actuator 480 may bepiezoelectrical bi-state actuator described below. In case ofmaterial-based switching by electro-active material, electric wiringconnects the electronics actuator connected to the control electronicsand presbyopia correcting optical element.

The controller 205′ provides paired instructions as shown by line 3″,one is audio instruction for the wearer and another wirelessly to thecontrol electronics 470. The wearer's audio instruction requires thewearer to view an object at near distance with downward gaze and anobject at far distance with straight ahead gaze. The pressure sensor 510provides “sensor signal at far” or “sensor signal at near” as inputsignal to the control electronics 470 at different gaze directions. Thewireless instruction for control electronics 480 instructs to outputactuation signal to the actuator 220 for switch SBS optical element 490to far optical power when the wearer is instructed to view the object atfar distance and near optical power when the wearer is instructed toview an object at near distance. A sensor signal is stored at eachviewing by the control electronics 270. The “teaching” program of thecontroller 205′ sends a set of paired instructions per certain algorithmto instruct the wearer to view the object at far distance with slightlyturning head to the right, left, up and down to create different gazedirections at far object viewing. The control electronics 470 storesdifferent sensor signals to form a “range of sensor signal at far.” Ateach gaze direction at far distance viewing, the controller 205′instructs the control electronics 470 to output “actuation signal forfar.” The result is that the control electronics 470 stores the matrixof the range of sensor signal at far and actuation signal for far. Theprocess is repeated for an object at near distance resulting in a matrixfor viewing an object at near distance with the result the matrix of therange of sensor signal at near and actuation signal for near. In theoperation mode the control electronics 470 then operates the matrixunder an algorithm to place a sensor signal at an appropriate range ofsensor signal and output the appropriate actuation signal for thepresbyopia correcting optical element to produce appropriate opticalpower that brings a viewing object in-focus for the given wearer.

FIG. 5A though FIG. 5D show piezoelectric bi-stable (bi-state) actuatorsthat switch between two stable states. Piezoelectric actuation is anattractive option for an electronic fluidic dynamic lens due to smalldimensions of piezoelectric actuator which allows its placement withinthe lens together with thin film rechargeable batteries and/or efficientsmall solar cells and compact microelectronics. The advantage of abi-state actuation is that no electric energy is consumed in maintainingthe actuator in either stable state, the electric energy is consumedonly for switching between the stable states. This allows the inventionto minimize electric energy used in operating a dynamic lens. Thepreferred embodiment of the present invention is to use a piezoelectricbi-stable actuator of bimorph (generally, a multimorph) construction incantilever action where piezoelectric bender in its unbent state is abeam or plate anchored at one end and demonstrate deflection of theother end with electrical field application. A bimorph bender includestwo piezoelectric layers to allow bender bending in opposite directionsunder a voltage of opposite signs, such bender is also calledbidirectional bender. In general, stable unbent bender state may be acurved shape.

FIG. 5A manifests a bi-state actuator in one the stable states, sayState A, where the piezoelectric bender plate 510 is in thecorresponding State A. The bender is attached to a flexible anchor 550of width W at one end, also called a flexible cantilever clamp, whichoffers a flexible bender clamping. This bender end is called “clampedend” and the other end that moves with a voltage application is calledthe “deflection end.” The permanent magnets 1, numbered 580 and 2numbered 570 are spaced by the distance T at distance L from theflexible anchor 550. They can be made of highly magnetically effectiveNd 58 material, for instance. The bender 510 in State A is in an unbendshape as the voltage is not applied to the bender in the stable state.The deflection end of the bender 510 includes magneto-active material560 that is attracted by the permanent magnets, magnet 580 in the StateA. Limiting members 590 and 600 support elements 570 and 580correspondently and they also control a deflection of the deflection endof the bender 590 when a voltage is applied and the bender 510 bends.

FIG. 5B demonstrates the bender 510 bending with applied voltage. Thelimiting member 590 limits a bender's bending down towards the plane ofthe magnet 580 thus assisting for maximum deflection of the deflectionend to reach the magnet 570. The distance T matches the benderdeflection magnitude. Upon bending, the deflection end of the bender 510overcomes the attraction (pulling) force of the magnet 580 and reachesthe magnet 570 thus creating a dominant attraction of the deflection endto the magnet 570. As an example, for the bender of length L≈4.5 mm,width W≈2.3 mm and bender thickness of about 0.35 mm, a deflection valueis at least 8 microns and force, so called blocking force, is ≈20 gramsof force for the applied voltage of 30 V. Regarding a permanent magnetmade of Nd 58 material with length 1 mm, width 1.8 mm and thickness 0.2mm, the pulling force is 15 grams of force. In this example, theblocking force of the bender 20 grams of force exceeds the pulling forceof the magnet of 15 grams of force thus allowing the deflection end toreach the opposite magnet and deliver the other stable state. If onemust have a different deflection magnitude, say, bender thicknessdoubles and length is 12 mm, the deflection becomes 100 microns andblocking force ≈55 grams of force. Then the magnet dimensions are alsoadjusted. Thus, by adjusting bender and magnet dimensions, one can meetthe requirements for the bender's deflection magnitude and to overcome amagnet pulling force upon bender bending.

FIG. 5C demonstrates the unbent bender 510 upon voltage termination withthe deflection end at the magnet 570. The bender takes its normal unbentshape of State B with a different angular position between the magnet570 and flexible anchor 550. This is because the bender's clamping endis in the flexible anchor 550. If an actuator chamber (not shown) isattached to the bender 510, the difference in bender position betweenStates A and B creates a difference in actuation chamber volume andallow to move the fluid between the actuation chamber and connected toit presbyopia correcting optical element. For instance, an actuator withdimensions of length L≈6.5 mm, width W≈3.5 mm and thickness T 1.5 mmwould produce a deflection Def≈25 microns. This, in turn, transfers afraction of microliter of the optical fluid between the actuationchamber and presbyopia correcting optical element. Such volume isadequate for SBS optical element switching in case of dynamic IOL anddynamic CL applications.

FIG. 5D demonstrates the bender 510 bending with applied voltage in theopposite direction from the one in the FIG. 5B. The limiting member 600limits a bender's bending up towards the plane of the magnet 570 toallow maximize a deflection of the deflection end to reach the magnet580. The deflection end of the bender 510 overcomes the attraction(pulling) force of the magnet 570 and reaches the magnet 580 thuscreating a dominant attraction of the deflection end to the magnet 580.Upon the voltage termination, the bender 510 takes a normal unbent shapeof the State A as shown on the FIG. 5A as the clamping end of the benderis at the flexible anchor 550 to allow for different angles of thebender plate.

It might be possible to introduce a transparent visual spectrumpiezoelectric for the actuator with Lithium niobate (LNO) material orthin layers of MoS₂, for instance. Transparency would make the dynamiclens more cosmetically appealing and increase flexibility in choosingbender design dimensions.

What is claimed is:
 1. An optimization system for presbyopia correction,comprising: a dynamic lens comprising: i) a sensor configured to measurea difference in an effect of an ocular element of an eye of a personviewing an object between a far distance and a near distance; ii) acontrol electronics configured to receive a sensor signal from thesensor; iii) an actuator configured to receive an actuation signal fromthe control electronics; and iv) a presbyopia correcting optical elementconfigured to communicate with the actuator for its setting in one of anoptical power for far distance and another optical power for neardistance; and a controller associated with and disposed separate fromthe dynamic lens, wherein the controller is configured to send a pairedinstruction synchronically to the person as an audio command to view theobject at one of the far distance and the near distance and to thecontrol electronics of the dynamic lens as a wireless command to sendthe actuation signal to the actuator for communication with thepresbyopia correcting optical element, wherein the audio command and thewireless command both correspond to the one of the far distance and thenear distance; wherein the control electronics is configured to receivethe wireless command from the controller and the sensor signal from thesensor, store the sensor signal, send the actuation signal to thepresbyopia correcting optical element and store the correspondingactuation signal; wherein the actuation signal for the far distancecommunicates to the presbyopia correcting optical element of the dynamiclens to set it for the optical power for far distance to bring theobject at the far distance in-focus; and wherein the actuation signalfor the near distance communicates to the presbyopia correcting opticalelement of the dynamic lens to set it for the another optical power fornear distance to bring the object at near distance in-focus.
 2. Theoptimization system for presbyopia correction of claim 1, wherein thefar distance is defined as 2 meters and beyond, and wherein the neardistance is defined as 0.5 meter and closer.
 3. The optimization systemfor presbyopia correction of claim 2, wherein the paired instructioncomprises a plurality of paired instructions relating to one of the fardistance or near distance, wherein each audio command of a plurality ofaudio commands includes a first instruction for the person to view theobject at either the far or the near distance and includes a secondinstruction for the person to change a gaze direction either right,left, up or down.
 4. The optimization system for presbyopia correctionof claim 3, wherein the gaze direction is changed by the head tilt ofthe person either right, left, up or down
 5. The optimization system forpresbyopia correction of claim 3, wherein a plurality of wirelesscommands are associated with the plurality of audio commands, whereinthe control electronics is configured to store a matrix of a pluralityof sensor signals and actuation signals corresponding to the same fardistance or near distance.
 6. The optimization system for presbyopiacorrection of claim 2, wherein the dynamic lens is an eyewear lens. 7.The optimization system for presbyopia correction of claim 2, whereinthe dynamic lens is an intraocular lens.
 8. The optimization system forpresbyopia correction of claim 2, wherein the dynamic lens is a contactlens.
 9. A method of optimization for presbyopia correction, comprising:providing a dynamic lens comprising: i) a sensor configured to measure adifference in an effect of an ocular element of an eye of a personviewing an object between a far distance and a near distance; ii) acontrol electronics configured to receive a sensor signal from thesensor; iii) an actuator configured to receive an actuation signal fromthe control electronics; and iv) a presbyopia correcting optical elementconfigured to communicate with the actuator for its setting in one of anoptical power for far distance and another optical power for neardistance; and providing a controller associated with and disposedseparate from the dynamic lens, wherein the controller is configured tosend a paired instruction synchronically to the person as an audiocommand to view the object at one of the far distance and the neardistance and to the control electronics of the dynamic lens as awireless command to send the actuation signal to the actuator forcommunication with the presbyopia correcting optical element, whereinthe audio command and the wireless command both correspond to the one ofthe far distance and the near distance; wherein the control electronicsis configured to receive the wireless command from the controller andthe sensor signal from the sensor, store the sensor signal, send theactuation signal to the presbyopia correcting optical element and storethe corresponding actuation signal; wherein the actuation signal for thefar distance communicates to the presbyopia correcting optical elementof the dynamic lens to set it for the optical power for far distance tobring the object at the far distance in-focus; and wherein the actuationsignal for the near distance communicates to the presbyopia correctingoptical element of the dynamic lens to set it for the another opticalpower for near distance to bring the object at near distance in-focus.installing the dynamic lens at the eye of the person; sending, via thecontroller while utilizing the control electronics in an optimizationmode, the paired instruction comprising the audio command to the personand the wireless command to the control electronics; storing, via thecontrol electronics, the sensor signal that is associated with thewireless command; and sending the actuator signal to the dynamic lensbased on the sensor signal while utilizing the control electronics in anoperation mode.
 10. The method of optimization for presbyopia correctionof claim 9, wherein the far distance is defined as 2 meters and beyond,and wherein the near distance is defined as 0.5 meter and closer. 11.The method of optimization for presbyopia correction of claim 10,wherein the paired instruction comprises a plurality of pairedinstructions relating to one of the far distance or near distance,wherein each audio command of a plurality of audio commands includes afirst instruction for the person to view the object at either the far orthe near distance and includes a second instruction for the person tochange a gaze direction either right, left, up or down.
 12. The methodof optimization for presbyopia correction of claim 11, wherein the gazedirection is changed by the head tilt of the person either right, left,up or down
 13. The method of optimization for presbyopia correction ofclaim 11, wherein a plurality of wireless commands are associated withthe plurality of audio commands, wherein the control electronics isconfigured to store a matrix of a plurality of sensor signals andactuation signals corresponding to the same far distance or neardistance.
 14. The method of optimization for presbyopia correction ofclaim 9, wherein the dynamic lens is an eyewear lens
 15. The method ofoptimization for presbyopia correction of claim 9, wherein the dynamiclens is an intraocular lens.
 16. The method of optimization forpresbyopia correction of claim 9, wherein the dynamic lens is a contactlens.